EP2388028A1 - Procédé destiné au fonctionnement d'un système de pompe - Google Patents

Procédé destiné au fonctionnement d'un système de pompe Download PDF

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Publication number
EP2388028A1
EP2388028A1 EP10075214A EP10075214A EP2388028A1 EP 2388028 A1 EP2388028 A1 EP 2388028A1 EP 10075214 A EP10075214 A EP 10075214A EP 10075214 A EP10075214 A EP 10075214A EP 2388028 A1 EP2388028 A1 EP 2388028A1
Authority
EP
European Patent Office
Prior art keywords
piston
pressure
pump
working
phase
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP10075214A
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German (de)
English (en)
Inventor
Jörg Hering
Andreas Arndt
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Berlin Heart GmbH
Original Assignee
Berlin Heart GmbH
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Berlin Heart GmbH filed Critical Berlin Heart GmbH
Priority to EP10075214A priority Critical patent/EP2388028A1/fr
Publication of EP2388028A1 publication Critical patent/EP2388028A1/fr
Withdrawn legal-status Critical Current

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Classifications

    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B49/00—Control, e.g. of pump delivery, or pump pressure of, or safety measures for, machines, pumps, or pumping installations, not otherwise provided for, or of interest apart from, groups F04B1/00 - F04B47/00
    • F04B49/20—Control, e.g. of pump delivery, or pump pressure of, or safety measures for, machines, pumps, or pumping installations, not otherwise provided for, or of interest apart from, groups F04B1/00 - F04B47/00 by changing the driving speed
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/104—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body
    • A61M60/109—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/424—Details relating to driving for positive displacement blood pumps
    • A61M60/427—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/50—Details relating to control
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/538—Regulation using real-time blood pump operational parameter data, e.g. motor current
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/845—Constructional details other than related to driving of extracorporeal blood pumps
    • A61M60/851—Valves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B2201/00—Pump parameters
    • F04B2201/02—Piston parameters
    • F04B2201/0202—Linear speed of the piston
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B2201/00—Pump parameters
    • F04B2201/02—Piston parameters
    • F04B2201/0203—Acceleration of the piston

Definitions

  • the invention is in the field of precision engineering and electrical engineering and is particularly concerned with a control method by means of which a complex pump system is to be controlled.
  • the invention is advantageously usable in the medical field.
  • An embodiment of such a heart typically includes a diaphragm pump that is within or may be disposed outside of a body and connected to the bloodstream via a suction port and an ejection port.
  • the pump is designed as a membrane pump, bag pump or a similar design with a drive space and a blood delivery space, which are separated by a movable membrane.
  • the drive space can be pressurized by means of a working pump, so that the position of the membrane can be selectively changed by the control of the drive pressure in order to generate overpressure or underpressure in the blood delivery space and thus to suck blood out of the blood circulation or expel it into it.
  • Valve-controlled, blood can be sucked through a valve during diastole and expelled through another valve during systole.
  • the corresponding blood pump should be set up in such a way that in its operation it can be adapted to the heart rate of the patient, to the required blood pressure and to the volume to be delivered.
  • a membrane control is required, which takes into account the inflow and outflow conditions on the blood side, that the membrane is expelled uniformly in both directions.
  • phase position of the cyclic diaphragm pump activity can also be adapted to the heartbeat of the patient.
  • the control of the working pump is designed according to the requirements.
  • it is here a complex, very fast and dynamic control option necessary, the reaction and readjustment possible within a Cycle of the working pump allowed. This is particularly important for small volume blood pumps, such as 10 ml, such as those used in infants.
  • the present invention is therefore based on the object to provide an operating method for a pump system of the type mentioned, which allows the simplest possible means an effective and fast-acting, dynamic control of the pump system.
  • the invention provides a method for operating a pump system with a designed as a piston pump working pump having an oscillatable by means of a drive unit between two reversal points in a pressure chamber working piston, wherein the piston pump is driven such that the drive piston in each case after passing through a reversal point Go through the acceleration phase and then delayed to the end of the specified path.
  • the invention also provides, in an advantageous embodiment, a method for operating a cardiac pump system with a pulsatile membrane blood pump for alternately aspirating and expelling blood in the bloodstream of a patient, which is drivable by means of a pressure line to the working pump, in each case after passing through a reversal point before reaching the Maximum or minimum pressure, a speed of the working piston of the working pump is reached, the amount is greater, in particular at least 10%, advantageously more than 30%, more advantageously more than 50% greater than the speed when reaching the extreme pressure.
  • the working piston is accelerated as quickly as possible after passing through a reversal point and thus in minimal time the next working stroke passes so far that a corresponding pressure in the pressure chamber is established.
  • This is particularly advantageous for small pumps whose volume is smaller in relation to the volume of the pressure lines than in large pumps and with which a rapid pressure build-up in the overall system is correspondingly more difficult.
  • Benefits also arise with pumps that are to be operated at high rates, as the pump driving the compressed air acts delayed on the air hose to the blood pump membrane.
  • An advantageous embodiment of the invention provides that energy is supplied to the working piston at least in a first, immediately adjacent to a reversal point path area without a speed limit.
  • This measure may mean, for example, that the drive unit contains no control / regulation of the speed, in the case of a rotating drive motor according to no speed control and no speed limitation.
  • the power of the power plant may instead be controlled or regulated.
  • the working piston can be maximally accelerated, especially in the first part of the movement of a working stroke, if No braking back pressure has yet built up in the pressure chamber.
  • the elastic energy of the acting as a gas spring pressure space is utilized to the initial acceleration of the working piston.
  • the working pump which drives the membrane blood pump via a pressure line, in turn by means of a drive unit oscillating drivable working piston, wherein the drive unit is controlled with respect to its torque and / or its power as a target size.
  • the energy transferred to the working piston by the pressure chamber acting as a gas spring is difficult to take into account in the control, but overall it is important to generate high dynamics to use as many resources as possible to accelerate the piston. Therefore, offers a torque or power control, so that the piston is particularly accelerated in the initial phase after passing through a reversal point by the residual pressure assistance. This allows operation of the pump even at high rates (up to 150 cycles per minute) and high strokes.
  • the further velocity profile of the piston is essentially determined by the impressed, predetermined power or the torque of the engine and, in addition, by the build-up counter-pressure.
  • the mechanical design of the piston may consist in a cylindrical piston which slides sealingly within a cylinder, or in the drivable bottom of a bellows or the like.
  • the piston drive can be realized by means of an electric rotary motor, for example by driving a threaded spindle by means of the motor, wherein the piston is connected to a spindle on the axially movable, rotatably mounted threaded nut.
  • an electric motor can be controlled in a particularly simple manner by means of an impressed current intensity profile predetermined for a power stroke or a duty cycle of the drive piston.
  • the dependence of the current intensity of the traversed piston travel or the rotation angle of the motor shaft or from the time since the last piston reversal time.
  • Such control is common in power electronics and easy to build.
  • the current to be impressed can also be specified in a control process. It may be constant throughout the piston drive during one cycle, or may periodically follow a current / path or current / time profile.
  • the invention can also provide that, in the case of the current intensity course to be determined, measured values from which deviations of the actual values from the setpoint stroke and the setpoint rate can be determined or the deviations determined are taken into account.
  • the motor is controlled by means of an at least temporarily linear current intensity curve.
  • This can have, for example, in at least one of the two cyclically recurring movement phases of the piston - in systole and / or diastole - a linear rise ramp. This means that during the piston acceleration, which takes place due to the residual pressure energy, the control current over the ramp is slowly increased. This limits mechanical loads on the system.
  • the current to drive the electric motor for the rest of the movement phase can either be kept constant or continue to increase linearly, for. B. with a lower slope than during the initial ramp. This may be useful because, during the passage of a cycle, the backpressure that is to be overcome by the piston increases, and accordingly, with a constant flow, the speed of the electric motor would decrease because of the resistance. Due to the additional increase, the speed profile can be individually adapted to the needs.
  • the movement speed of the motor and / or the piston in particular the rotational speed of the motor, is detected.
  • the mentioned movement variables are essentially dependent on the control current of the motor and the mechanical boundary conditions of the engine and piston, but substantially also of the pressure built up in the pressure chamber of the working pump at the beginning of the piston movement to its end. This results in the detection of said movement quantities information that can be used to control the pump system. If the timing of the measurement of the amount of movement / speed of the engine is properly selected, this depends essentially on the initial acceleration of the piston by the residual pressure in the system or even only by the filling of the working space of the diaphragm pump.
  • the movement speed of the motor and / or the piston in particular the rotational speed of the motor, as well as the position of the working piston, is constantly detected.
  • These quantities can be evaluated cyclically at least once at a fixed cycle time during each suction and each pressure phase (diastole and systole). It can be provided that the measurement of the speed of movement of the motor and / or the piston takes place at a time, too the measured quantity depends essentially on the pressure generated by the working pump.
  • the drive piston position measurements can be used to predict a drive train history / current history for the next cycle of the work pump.
  • Pressure readings can be used to control a control valve that adjusts the amount of gas in the pressure space of the work pump and in the gas lines.
  • An advantageous implementation of the invention provides that a control valve, which connects the pressure chamber of the working pump with a compensating volume, is driven cyclically as a function of determined deviations of the measured movement speeds or rotational speeds or the measured pressure profiles of pressure values derived therefrom from predetermined reference values.
  • the control valve can thus be discharged from the working space of the working pump, the working gas, such as air, at a certain time in the compensating volume, for example, the environment of the pump at atmospheric pressure, or it can be sucked in the intake phase via the control valve air.
  • the total amount of gas in the system is regulated in each case during a cycle, so that the average pressure in the system can be controlled in each case by appropriate actuation of the control valve.
  • the opening duration of the control valve is advantageously predetermined in each case at the beginning of the respective intake or pressure phase.
  • the maximum speeds of the engine in the pressure and in the suction phase are determined and compared with each other. From the respectively achieved maximum speeds of the engine results in the achieved membrane deflection of the diaphragm pump. This depends inter alia on the support of the piston acceleration by the residual pressure in the working volume.
  • These measured variables or, for example, their difference can / can be used as an input variable for a control of the control valve or can also be compared with reference values in order to effect a readjustment of the control valve in the event of the deviation.
  • control variable for a control valve is calculated from the two rotational speeds which are measured in systole and diastole at the time when the pressure has reached the average system pressure, in particular from the difference between these two rotational speeds. which connects the working space of the working pump for a controllable time during systole and diastole, in particular in each case after passing through the pressure zero value, with a compensating volume.
  • the power to be controlled or the target torque of the electric motor or the corresponding time profile can be specified.
  • This size can also be changed during operation, for example, by raising a total current profile of the electric motor or selecting a different gradient in the course of a cycle before one cycle of the work pump.
  • Rate and total lift are adjusted to the available cycle time and the volume to be delivered by selecting the current profile.
  • To control or regulate the power / current can serve for a given stroke as the input of the controller when reaching the end position of the piston, a remaining time difference or, if the current is too low, at the end of the cycle time the remaining distance to the predetermined and not yet reached End position (reversal point) of the piston. Only when the piston has reached exactly the end position at the predetermined time, this control of the current profile remains inactive.
  • the invention also relates to a method in which a braking of the working piston movement is examined during the pump operation, at which position of the piston occurs and / or how strong the braking acceleration and that at a certain deviation from the normal behavior on the existence of a blockage of Pressure line or blood lines (cannulas) is detected. As a result, an alarm can be triggered automatically in the event of jamming of the pressure line or the cannulas.
  • the invention relates not only to a method of the type described also to a pump system operable with such a method with a membrane blood pump which is drivable by a working pump by means of a pressure line, wherein the working pump has a reciprocally driven by a drive unit piston in a cylinder, characterized by a means of a controller controllable control valve, which connects a pressure chamber of the working pump with a compensation volume.
  • Fig. 1 schematically shows a silhouette 1 of a person who is connected to an extracorporeal membrane blood pump 2, which via two connecting lines, an intake pipe and an exhaust pipe connected to the human bloodstream.
  • the membrane blood pump 2 is connected via a pressure line 3 to a working pump 4, which drives the diaphragm pump 2.
  • the work pump 4 is electrically powered by an energy source 5.
  • Such pumping systems may be fixed in place, but may be portable and, for example, carried by a patient in a backpack.
  • the power source 5 is then usually a battery that powers the motor of the work pump.
  • the work pump is usually a piston pump, which in the Fig. 2 is shown schematically and denoted by 4. It has a cylinder in which a piston 18 in the direction of the arrows 20, 20a between two reversal points oscillating or oscillating can be driven. With this oscillating movement, overpressure and underpressure are alternately generated in the pressure line 3, which also generates overpressure and underpressure in the drive space 16 of the diaphragm pump 2. If the working pump generates negative pressure, the membrane 12 is pulled in the direction of the arrow 13, so that a negative pressure arises in the working space 10, which leads to the suction of blood via the inflow line 6 in the direction of the arrow 7 and through the one-way valve 14.
  • the working space 10 is filled with blood in this way.
  • the flow velocity of the blood into and out of the working space 10 must be kept within certain limits. This makes special demands on the acceleration of the diaphragm 12 and thus on the performance of the working pump. 4
  • valve 14 closes.
  • the piston 18 has then reached its lower reversal point after a movement in the direction of the arrow 20a and moves upward in the direction of the arrow 20 in the course of a compression movement 12 moves in the direction of the arrow 17, and the working space 10 is compressed.
  • the valve 15 opens immediately or delayed at a certain preset release pressure and allows blood to flow through the discharge line 8 in the direction of the arrow 9. It is important that the piston pump 4 is strong enough in the compression phase to move the membrane vigorously in the direction of the arrow 17 up to its reversal point.
  • the working gas typically air
  • the cylinder bears the reference numeral 19 and is arranged such that the piston slides in it tightly.
  • the drive is provided by an electric motor 24, which drives a motor shaft 33 with a connection piece 25.
  • a threaded spindle 22 is connected, which is rotatably mounted in two bearings 26, 27 within a bearing block 28 in the cylinder 19.
  • the spindle cooperates with a threaded nut 23 which is rotatably mounted in the piston 18.
  • the spindle causes during rotation in a first direction an axial drive of the piston in the direction of the arrow 42, in the reverse direction of rotation, a drive of the piston in the direction of the arrow 32nd
  • the piston 18 compresses the pressure chamber 20 of the cylinder 19, so that the working gas, in particular air, is pressed through the port 21 into the pressure line 3 or sucked out of it.
  • the piston 18 is gas-tightly connected to a guide tube 29 into which the spindle 22 protrudes. In this way, the nut 23 can move along the entire spindle.
  • the guide tube 29 is optionally guided in a guide 30, which practically completely fills it when reaching the point of reversal of the piston in the compression phase. Thus, the dead space of the cylinder 19 is minimized.
  • a spring 31 can be provided, which is compressed by the motor drive 24 via the spindle during the suction phase and additionally emits the stored energy to relieve the pressure on the piston during the pressure phase.
  • the current and / or power control 34 is shown schematically. This may, for example, provide a fixed, constant, or certain fixed curve (with respect to the piston travel or rotation angle of the spindle) to the motor 24.
  • the pressure represented by the curve 35, in the pressure chamber 20 of the working pump 4, and thus also in the pressure line 3 and in the drive chamber 16 of the blood membrane pump, maximum.
  • the piston has reached its reversal point after complete compression of the volume in the pressure space 20, and the blood is expelled from the working space 10 of the membrane blood pump.
  • the piston moves to initiate the suction phase in the direction of arrow 32 in Fig. 3 ,
  • the pressure 35 decreases very rapidly in this phase.
  • a significant proportion of the acceleration of the spindle contributes in this phase of the prevailing pressure in the pressure chamber 20, which drives the piston 18 in the direction of the arrow 32.
  • this acceleration can be fully effective, so that the speed of the spindle coincides with the falling pressure 35 a peak, visible in the curve 36 of Fig. 4 , having.
  • the mechanical acceleration is mainly due to the potential energy of the compressed gas, but depending on the slope of the ramp of the current strength in addition the electric drive.
  • the described control of the motor with a predetermined current waveform or electrical power curve ensures that the stored pressure in the gas pressure is fully utilized in reversing the direction of rotation of the drive motor and converted into an acceleration of the working piston and the spindle.
  • the system is not braked by a speed control in this phase.
  • This allows a very dynamic change between the pressure and suction phases.
  • the constant current control works in case of malfunctions such as blocking a cannula as a pressure control: Once a cannula is blocked, the speed of the spindle is reduced in the printing phase by increasing the pressure with constant torque, so that the blood flow decreases. The speed reduction can be monitored and used to detect cannula constriction and alarm triggering.
  • the absolute stroke of the pump is adjusted according to the pump size and the volume to be pumped. In conjunction with the set current profile and the achieved heart rate, the absolute throughput of liquid through the diaphragm pump is determined. Otherwise, the drive automatically adapts to each pump to be operated by the regulation. Is the impressed current / power too low in order to reciprocate the piston 18 between its planned reversal points in the given cycle time, this is registered by means of displacement / proximity sensors and leads to an increased current / power at the next working stroke of the piston, or if it is determined by means of a time measurement in that the piston is moved too fast, this results in a selection of a current profile with a reduced current / power for the next cycle of motion of the piston.
  • Fig. 5 shows schematically with a few details, the work pump with the cylinder 19, the piston 18, the discharge port 21 and the motor 22 driven by the spindle 22nd
  • the piston is shown in a randomly selected position, but two other possible positions 18 ', 18 "are shown by dashed lines, and proximity sensors 38, 39 in the form of Hall sensors are shown, which register where the piston 18 is located. at least if it is in the range of one of its reversal points.
  • the controller 34 is given a cycle time either via an input 40 or via the synchronization with the blood pressure of the patient continuously registered by the measuring device 41, in which the piston 18 must have covered a complete movement period.
  • a timing unit 42 indicates a time base, for example, the proximity switch 38 registers whether at the end of the cycle time the piston 18 has reached its position 18 '. If this is the case before the cycle time has elapsed, then for the next cycle the control current for the motor 24 is lowered slightly. If the piston does not reach the position 18 'in time, the current of the motor 24 is increased slightly or a current profile selected for the next cycle, which provides an increased current / time integral. An optionally predetermined current profile can also be raised or lowered altogether.
  • Corresponding measurements can also be carried out by the proximity switch 39 at the end of the suction phase.
  • the rotational speed of the spindle 22 is continuously measured by means of the speed measuring device 43.
  • the speed of the spindle 22 depends largely on the pressure in the pressure chamber 20 of the working pump, so that from the difference of the measured speeds in the systolic and diastolic phase at certain fixed cycle times, the deviation of the actual pressure of the mean target pressure in the pressure chamber 20 can be determined. If the pressure is too high, in the next cycle at the beginning of the compression phase the control valve 44 will be opened or opened longer than in the previous cycle. Thus, the working gas / air can flow out of the pressure chamber 20 for a while, so that the pressure built up thereafter remains slightly lower than in the previous cycle.
  • valve 44 may remain open for a while or be opened for a longer time than in the previous cycles in order to regulate the final pressure reached.
  • control mechanisms are used, on the one hand to regulate the speed by means of the set current, in addition, the average pressure in the suction and in the pressure phase is controlled within a cycle.
  • the impressed current intensity or the impressed current intensity profile is readjusted in accordance with the requirements.
  • FIG. 6 shows different current intensity curves over time with a ramp at the beginning of the piston movement and a constant 45 and a linear rising 46 current course thereafter. Corresponding curves can also be specified in the form of a current / piston stroke diagram.
  • FIG. 7 shows a three-dimensional representation of the working pump, in which a control valve 44 is provided on the end face of the cylinder 19, two magnetic displacement sensors 38,39 on the guide tube 29 and a Hall sensor 47 on the spindle 22.
  • the spindle 22 is designed as a ball screw drive.
  • the threaded nut in the piston 18 contains correspondingly spring-mounted guide balls.
  • the invention has a low measuring outlay, and it is particularly advantageous to save flow measurements and volume flow measurements on the system. Due to the dynamic control, the pump is able to operate in a range of about 10 to 80 milliliters per cycle in the diaphragm pump at a rate of Up to 140 to 150 times per minute, so that appropriate pumps can be used even in small children without problems.
  • the invention can be summarized as follows: The motor of a pneumatic piston pump is driven according to a speed profile, according to which the working piston is first moved at a high speed after an acceleration phase and then delayed to the end of the predetermined path.
  • Such a speed profile can be implemented particularly simply by controlling an electric motor of the pump with a predefined constant current.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Mechanical Engineering (AREA)
  • Hematology (AREA)
  • Cardiology (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • General Engineering & Computer Science (AREA)
  • External Artificial Organs (AREA)
  • Reciprocating Pumps (AREA)
EP10075214A 2010-05-20 2010-05-20 Procédé destiné au fonctionnement d'un système de pompe Withdrawn EP2388028A1 (fr)

Priority Applications (1)

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EP10075214A EP2388028A1 (fr) 2010-05-20 2010-05-20 Procédé destiné au fonctionnement d'un système de pompe

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Application Number Priority Date Filing Date Title
EP10075214A EP2388028A1 (fr) 2010-05-20 2010-05-20 Procédé destiné au fonctionnement d'un système de pompe

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EP2388028A1 true EP2388028A1 (fr) 2011-11-23

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Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102012207042A1 (de) * 2012-04-27 2013-10-31 Abiomed Europe Gmbh Pulsationsblutpumpe
EP2860399A1 (fr) * 2013-10-14 2015-04-15 ECP Entwicklungsgesellschaft mbH Procédé de fonctionnement d'un dispositif d'alimentation qui sollicite un canal avec un liquide, et dispositif d'alimentation
CN107456616A (zh) * 2017-08-04 2017-12-12 中国医学科学院阜外医院 心脏模拟设备
WO2019024111A1 (fr) * 2017-08-04 2019-02-07 中国医学科学院阜外医院 Dispositif de simulation cardiaque
EP3536955A1 (fr) * 2018-03-08 2019-09-11 Berlin Heart GmbH Dispositif d'entraînement pour une pompe à fluide à membrane et procédé de fonctionnement
CN112156254A (zh) * 2020-10-14 2021-01-01 北京航空航天大学 一种可反馈调节的体外循环人工心脏泵

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
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DE19649675A1 (de) * 1996-01-30 1997-07-31 Penn State Res Found Kunstherz-Bremssystem
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US9555173B2 (en) 2012-04-27 2017-01-31 Abiomed Europe Gmbh Pulsatile blood pump
DE102012207042A1 (de) * 2012-04-27 2013-10-31 Abiomed Europe Gmbh Pulsationsblutpumpe
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CN105917118A (zh) * 2013-10-14 2016-08-31 Ecp发展有限责任公司 用于操作向通道供给液体的供给装置的方法，以及供给装置，中空导管和导管泵
JP2017500068A (ja) * 2013-10-14 2017-01-05 エーツェーペー エントヴィッケルングゲゼルシャフト エ 導管に液体を供給する供給装置の動作方法および供給装置、中空カテーテル、およびカテーテルポンプ
EP3594500A1 (fr) * 2013-10-14 2020-01-15 ECP Entwicklungsgesellschaft mbH Procédé de fonctionnement d'un dispositif d'alimentation qui sollicite un canal avec un liquide, dispositif d'alimentation et pompe à cathéter
WO2015055515A1 (fr) * 2013-10-14 2015-04-23 Ecp Entwicklungsgesellschaft Mbh Procédé de fonction d'un dispositif d'alimentation qui alimente un conduit avec un liquide, dispositif d'alimentation, cathéter creux et pompe de cathéter
US10195323B2 (en) 2013-10-14 2019-02-05 Ecp Entwicklungsgesellschaft Mbh Method for operating a supply device which supplies a liquid to a channel, and supply device, hollow catheter, and catheter pump
EP2860399A1 (fr) * 2013-10-14 2015-04-15 ECP Entwicklungsgesellschaft mbH Procédé de fonctionnement d'un dispositif d'alimentation qui sollicite un canal avec un liquide, et dispositif d'alimentation
EP4033100A1 (fr) * 2013-10-14 2022-07-27 ECP Entwicklungsgesellschaft mbH Procédé de fonctionnement d'un dispositif d'alimentation qui sollicite un canal avec un liquide, dispositif d'alimentation, catheter creux et pompe à cathéter
US10780205B2 (en) 2013-10-14 2020-09-22 Ecp Entwicklungsgesellschaft Mbh Method for operating a supply device which supplies a liquid to a channel, and supply device, hollow catheter, and catheter pump
CN107456616A (zh) * 2017-08-04 2017-12-12 中国医学科学院阜外医院 心脏模拟设备
WO2019024111A1 (fr) * 2017-08-04 2019-02-07 中国医学科学院阜外医院 Dispositif de simulation cardiaque
EP3536955A1 (fr) * 2018-03-08 2019-09-11 Berlin Heart GmbH Dispositif d'entraînement pour une pompe à fluide à membrane et procédé de fonctionnement
US10441695B2 (en) 2018-03-08 2019-10-15 Berlin Heart Gmbh Drive device for a membrane fluid pump and operating method
CN111819362A (zh) * 2018-03-08 2020-10-23 柏林心脏有限公司 用于隔膜流体泵的驱动装置和操作方法
US11141579B2 (en) 2018-03-08 2021-10-12 Berlin Heart Gmbh Drive device for a membrane fluid pump and operating method
WO2019170553A1 (fr) * 2018-03-08 2019-09-12 Berlin Heart Gmbh Dispositif d'entraînement pour une pompe de fluide à membrane et procédé de fonctionnement
CN111819362B (zh) * 2018-03-08 2022-09-27 柏林心脏有限公司 用于隔膜流体泵的驱动装置和操作方法
CN112156254A (zh) * 2020-10-14 2021-01-01 北京航空航天大学 一种可反馈调节的体外循环人工心脏泵
CN112156254B (zh) * 2020-10-14 2022-02-22 北京航空航天大学 一种可反馈调节的体外循环人工心脏泵

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